|Número de publicación||US5496351 A|
|Tipo de publicación||Concesión|
|Número de solicitud||US 08/318,463|
|Fecha de publicación||5 Mar 1996|
|Fecha de presentación||5 Oct 1994|
|Fecha de prioridad||5 Oct 1993|
|También publicado como||DE69426323D1, DE69426323T2, EP0655260A2, EP0655260A3, EP0655260B1, US5693075|
|Número de publicación||08318463, 318463, US 5496351 A, US 5496351A, US-A-5496351, US5496351 A, US5496351A|
|Inventores||Gianni Plicchi, Giorgio Corbucci|
|Cesionario original||Sorin Biomedica S.P.A.|
|Exportar cita||BiBTeX, EndNote, RefMan|
|Citas de patentes (2), Otras citas (14), Citada por (110), Clasificaciones (11), Eventos legales (6)|
|Enlaces externos: USPTO, Cesión de USPTO, Espacenet|
1. Field of the Invention
The present invention refers in general to the determination of the myocardial function by the use of accelerometric devices.
2. Background of the Invention
U.S. Pat. No. 5,304,208, incorporated herein by reference, describes a pacemaker of the rate-responsive type which includes an accelerometric sensor located in the pacing lead with the aim of making the pacing rate of the device depend on a parameter obtained by processing the signal of the Natural Heart Acceleration (NHA). U.S. Pat. No. 5,304,208 discloses the analysis of the entire signal which describes the NHA, and in particular the identification of the peak value, the calculation of the mean, and the possible identification of the atrial and ventricular phases; contemplating the utilization of the NHA signal for both single-chamber and dual-chamber cardiac pacemakers, for antiarrhythmic pacing devices and for implantable defibrillators, i.e., the so-called Pacer Cardioverter Defibrillators (PCDs). U.S. Pat. No. 5,304,208 differentiates the principles of measuring acceleration from those of measuring the blood pressure inside the ventricle and its derivative with respect to time. The same considerations can be extended to U.S. Pat. No. 4,936,304, where a cardiac pacemaker of the rate-responsive type is assumed, in which the pacing rate is regulated by the processing of intramyocardial stresses measured by inserting inside the myocardium a pressure meter of the type conceptually similar to the one used for measuring the ventricular blood pressure. Consequently, well documented from U.S. Pat. No. 5,304,208 is the substantial difference existing between the measurement of acceleration, where the accelerometric sensor is contained in an undeformable capsule, and the pressure transducers that are equipped with a deformable membrane which enables the pressure to be transduced into a measurable force.
The limitations in the use of the NHA signal according to the procedure described in U.S. Pat. No. 5,304,208 are based on the fact that, since the cardiac mass is subject to overall movements deriving from inertial reactions which are difficult to foresee and are due to the simultaneous phases of aortic and pulmonary ejection, and in association with these the movements themselves of the specific segment of endocardium in which the lead is inserted with the accelerometer, it may prove difficult from the mere reading of the accelerometric signal of NHA as a whole, to deduce which pan is due to the overall movement and which expresses the muscular dynamics of the myocardium underlying the surface of the endocardium on which the accelerometer is set.
The present invention, therefore, sets itself the purpose of further improving upon U.S. Pat. No. 5,304,206 above all as far as the precision and reliability of the sensing action is concerned. According to the present invention, this purpose is achieved in a device having the characteristics referred to specifically in the claims that follow. The invention refers also to the corresponding method for determining the myocardial function.
In the form of implementation preferred at the moment, the invention includes an implantable micro-accelermeter and corresponding electronic circuits located on a lead, e.g., as described in U.S. Pat. No. 5,304,208. Further, the continuous measurement of the electrocardiogram is made with electrodes, one of which coincides with the container of the accelerometer, providing identification of one or more segments (either phases or intervals) of the signal that indicates the NHA of particular importance for determining the cardiac function. For instance, one can isolate an interval of time which comprises a phase of the cardiac cycle, e.g., the isovolumetric pre-ejection phase. Since total movements of the cardiac mass as a reaction to the expulsion phases do not occur, the signals that may be detected by the accelerometer derive solely from the contraction of the myocardial wall which precedes ejection.
Likewise, it is possible to isolate another time interval which contains the isovolumetric relaxation phase. Since there do not occur total movements of the cardiac mass as a whole, the accelerometric signals are indicative of the elastic behavior of the ventricular wall. Furthermore, from the analysis of the ventricular ECG, it is possible to recognize (using techniques which themselves are already known) the presence of arrhythmias which, since they alter the physiological rhythms and the physiology of cardiac mechanics, may be at the root of errors of determination of the myocardial function. The recognition of these arrhythmias makes it possible to isolate, in the context of the accelerometric signal, the anomalies induced by them, so enabling both their elimination and a separate analysis.
In particular, the present invention makes it possible to distinguish, in the NHA signal, the acceleration of the endocardial wall on which the electrode is fixed from the acceleration that the mass of the heart as a whole undergoes. The foregoing is of major importance for the purposes of measuring a quantity that represents the contractile function of the heart which, for its definition, must be evaluated in a way that is independent of the pressure load that the heart is required to overcome during the ejection phase, and hence exclusively during isovolumetric phases.
As provided above, an important characteristic of the invention consists in associating to the measure of endocardial acceleration one or more time intervals which comprise the phases during which each cavity of the heart is virtually immobile (by analysis of the endocardial ECG), for example the phase of isovolumetric contraction, in which the only mechanics that occurs consists in the tensioning of the ventricular walls in order to prepare the ventricles for the subsequent ejection phase. This phase is defined in physiology as the phase of isovolumetric contraction and is associated with displacements of the endocardium of the order of only one mm during the increase in intraventricular blood pressure.
Typically in the normal heart at rest, the phase of isovolumetric contraction starts a few milliseconds after the QRS of the endocardial ECG and lasts for not longer than approximately two hundred msec. In the paced heart this interval, measured starting from the pacing spike, may be even as much as approximately two hundred and fifty msec. The duration of the above-mentioned phase is not constant and varies as a function of parameters, such as cardiac rhythm and physical activity. The apparent contrast between the formal identification of this phase as isovolumetric and the minimal movement of the endocardial wall is physiologically explained by the retroflexion of the tricuspid valve in the right atrium, which causes a modest variation in the volume of the ventricular cavity.
The physiological definition of contractility is referred to the elementary unit of the cardiac muscle and consists in the velocity of the contractile element (VCE) in the absence of load. Therefore, measuring acceleration in this phase, in which the ventricular work is represented by the minimal variation in volume associated to the retroflexion of the flaps of the tricuspid valve and by the low pressure present physiologically in the right atrium into which the same tricuspid valve is retroflexed, can be used to represent, in an original and innovative way, the contractile function of the heart.
In similar fashion, the description of the motion of the endocardial wall expressed by NHA during the phase of isovolumetric relaxation is an effective way of representing the compliance of the myocardial wall, which is an important index of cardiac function. The advantage of measuring the characteristics of the motion detected with a direct physical measurement of the acceleration of a point of the endocardium is all the more evident when it is considered that the methods currently used in clinical practice for estimating the maximum intrinsic volume of the myocardium, VMAX, are based on the extrapolation of the first derivative of the ventricular blood pressure dP/dt referred to the isovolumetric pressure. This model requires the assumption of a precise geometry of the cardiac mass and endodiastolic volumes to allow calculation of the intramyocardial stresses with the aim of making available parameters that might be compared between different patients. Unfortunately, the unavailability of a truly reliable geometric model and the documented lack of homogeneity of the stresses within the myocardial wall, which differentiates the behavior of the layers close to the endocardium from those close to the epicardium, nullifies all the extrapolations that have the ultimate aim of identifying the contractile element velocity, VCE, universally acknowledged as expressing contractility.
The solution of the present invention enables direct measurement in loco of the acceleration, for example, in the isovolumetric contraction phase, and is superior to indirect methods of measurement. The range of application of the present invention is considerably greater than that of the rate-responsive pacemaker and extends to the vast sector of cardiovascular illnesses in which it proves advantageous, if not essential, to have available a continuous measurement of the myocardial function. The transcutaneous telemetric transmission of the accelerometric signal together with the endocardial ECG to an appropriate external recording monitor (built using miniaturized techniques) allows display of the current value of the contractile function and the memorization of the trend of these signals for long time intervals, guides the cardiologist in drug therapy and other medical treatment of the patient, and may even furnish audio-optical warnings that prompt the patient to take the prescribed drugs. Further, it is possible to automatically manage the continuous infusion of drugs through external pumps controlled by these telemetric signals. Finally, it is possible to integrate the device for measuring and processing acceleration and the endocardial ECG in the electronics of an implantable infusion pump that may be recharged externally according to technologies already present on the market, but which do not envisage control sensors.
The invention described above can be utilized in single- or dualchamber pacemakers of the rate-responsive type where, unlike what is described in U.S. Pat. No. 5,304,208, the endocardial acceleration is used only in the phase of isovolumetric contraction. Finally, the present invention can be utilized in Pacer Cardioverter Defibrillators or PCDs, where the solution according to the invention proves extremely sensitive in the identification of tachycardias that are haemodynamically not efficient.
In brief, the solution according to the invention envisages associating with the NHA signal the recording of the endocardial ECG, with the aim of separating from the entire periodic beat-to-beat NHA signal (NHA(t)) one or more time intervals, for example the time interval which contains the isovolumetric contraction phase. This time interval can be chosen, for instance, as approximately two hundred msec following on the spontaneous QRS and approximately two hundred and fifty msec following on a possible cardiac pacing pulse delivered through the tip of the lead located in the apex of the fight ventricle, which contains also the accelerometric sensor. The duration of this interval can of course be automatically adapted (e.g., reduced) according to the heart rate.
On the endocardial acceleration signal sensed in this phase of duration T it is possible to carry out, either singly or in association, any type of mathematical processing, such as, for example, the peak-to-peak value, which indicates the maximum variation of the signal in that interval, and/or the peak value, and/or the rectified mean value expressed by the relation: ##EQU1## where this value is directly correlated to the energy content. Other processing operations are of course possible, including derivations and/or integrations, also cascaded ones, to obtain signals of velocity and displacement.
In the form of implementation at present preferred, a device for the bi-directional transcutaneous telemetric transmission of data is associated with the device for sensing and processing acceleration and ECG, with the dual purpose of transmitting to an external receiver device both the endocardial ECG and the acceleration as sensed and/or as data processed in the phases identified starting from the ECG, as previously described. In the opposite direction the external device makes it possible to program the calibrations and to drive the implanted device in a complete way.
To this implanted system for measuring, processing, and transmitting data, which can mean for the cardiologist a product that can be of support in conventional therapeutic choices it is possible to associate different therapeutic devices, either implantable or otherwise, where in the case of implantable ones the circuitry, mechanics and batteries can be contained in the same device that comprises the means of measuring, processing and transmitting bi-directional data.
In particular, this category of integrated devices includes a single- or dual-chamber cardiac pacemaker of the rate-responsive type driven by the processing of the heart acceleration signal in the isovolumetric contraction phase, associated or otherwise to other activity sensors. In this case, the ventricular lead performs the triple function of containing the accelerometer, the pacing electrodes, and the endocardial ECG sensing electrodes, possibly coinciding with the pacing electrodes.
In identical manner in the sector of the electrical therapy of cardiac arrhythmias, the device for sensing, processing and telemetering of acceleration and ECG can be integrated in the structure of a PCD with the purpose of confirming the possible haemodynamic inefficiency of serious atrial and/or ventricular tachyarrhythmias requiring sequences of electrical pulses for therapeutic purposes and/or defibrillation shock.
Also, the usual presence of a lead implanted in the right ventricle renders integration in existing technologies of this sector simple; the high percentage of false positives (15-20%) in which a defibrillation shock is needlessly delivered renders highly important the possibility of associating a mechanical parameter, such as that derivable from heart acceleration, to the analysis of the ECG to confirm the inefficiency of the cardiac pump and hence the activation of the therapeutic electrical sequences.
In the sector of implantable pumps for the continuous administration of medications, the utilization of the invention makes it possible to achieve in a precise and reliable way a continuous dosage regulated by the need for cardio-active drugs. In this case, the lead in the right ventricle is implanted only with the aim of sensing acceleration and endocardial ECG even though it is possible to combine the latter together with the pathway used for intravenous infusion of the drug. The electronic circuitry of the device in this case is integrated in the circuitry of the pump which already conventionally envisages the utilization of a bi-directional telemetry device.
In the example of application considered at the moment to be of greater interest, the invention refers to an implantable sensor of the contractile function of the heart on which it is applied, or to the passive telemetric monitoring of this function, or to the determination of the pacing rate in an implantable pacemaker of the rate-responsive type, or to the determination of the moment in which to make the discharge or the therapeutic stimulation in a PCD, or to control actively the supply of cardio-active drugs through external or implantable infusion pumps, where the functions referred to above can be performed singly or in association as required in any combination and with any number thereof.
In this case, the sensor to which the invention refers consists of a micro-accelerometer located inside the tip of a lead of the type used in implantable pacemakers or defibrillators and which combines with the function of detecting acceleration that of sensing the endocardial ECG between the tip and a second electrode, which can consist of a ring set at a short distance from the tip, or the implanted metal container itself (containing the necessary circuitry or battery) in which the lead referred to above is inserted, in a way similar to the procedure followed in the system of cardiac pacemakers, in the apex of the right ventricle, so that in certain of the envisaged applications, such as the rate-responsive pacemaker and the PCD, it is possible to associate with the passive function of measuring acceleration and of sensing the endocardial ECG also the active function of pacing and defibrillation of the heart.
FIG. 1 illustrates schematically the general use of a device according to the invention;
FIG. 2 illustrates, in the form of a circuit block diagram, the internal structure of the device according to the invention;
FIGS. 3a and 3b consist of six time diagrams, a1, a2, a3, and b1, b2, b3, which illustrate the typical pattern of certain signals indicating cardiac activity; and
FIG. 4 is an ideal representation of the blood pressure wave recorded in the right side of the heart.
The invention will now be described purely with the purpose of providing an example of application, without this application, however, in any way constituting a limit for the invention. In FIG. 1, block 1 represents an electronic interface device according to the invention having the purpose of sensing myocardial acceleration in at least one isovolumetric phase and of processing parameters derived therefrom. In a manner which will be described in more detail hereafter, electronic interface 1 receives, amplifies and filters the signal generated by the accelerometer and, triggered by endocardial ECG or pacing pulse, computes the peak endocardial acceleration during the isovolumetric phase according to a design known to those of skill in the art. This device is to be implanted in the body of a patient P.
Block 11 represents a conventional bi-directional transmission module for bi-directional data transmission between the inside and outside of the body of the patient for the purpose of monitoring myocardial acceleration and derived parameters of cardiac functionality, and for the purpose of programming operation of block 1. Such devices have been commonly employed for programming and for transcutaneously transmitting and receiving data from cardiac pacers and implantable defibrillators. Blocks 1 and 11 are preferably integrated in a single implantable device and are intended to operate together with a therapeutic device D, which may be a cardiac pacer, a PCD or a drug infusion pump. Device D is preferably implantable and, if possible, integrated with the device consisting of blocks 1 and 11. The device D is intended to carry out on the patient P a drug-administration intervention and/or an intervention of an electrical nature according to the processing of the myocardial acceleration and of the endocardial ECG performed by block 1 and block 11. It is, however, possible to create an implantable device consisting solely of blocks 1 and 11 with the exclusive aim of monitoring myocardial function. The device D can be replaced, for example, by a rate-responsive cardiac pacemaker or by an implantable cardiac defibrillator, or by a device for dosed administration of drugs. In any case, the characteristics and modes of operation of the device D are known to those of skill in the art. The characteristics of the device D, as well as the way in which it is connected to the body of the patient P, are not of themselves important for the purpose of understanding the invention.
In general, block 1 is connected to a lead, having a tip C inserted in the myocardium of patient P according to known criteria. The connection is made via input terminals 2 where, in 2a, there is present an endocardial ECG signal, and in 2b, an endocardial acceleration, NHA(t), measured by a sensor, such as the one described in U.S. Pat. No. 5,304,208. These signals are referred to a second reference electrode consisting of a ring located on the lead or of the metal container of the therapeutic device D, normally implanted subcutaneously.
Typical patterns of the signals are shown in diagrams a1 and b1 (ECG), and a2 and b2 (NHA(t)) of FIGS. 3a and 3b Diagrams a3 and b3 represent the right ventricular pressure signal (RVP) sensed with a known transducer external with respect to the system described. The time scales of the superimposed diagrams coincide with one another. These signals were obtained in the course of experimental tests on animals (sheep) and refer to a situation of rest (Diagrams a1, a2 and a3) and to a pharmacological pacing phase carried out with intravenous injection of doubutamine (Diagrams b1, b2 and b3).
The diagram of FIG. 4 illustrates schematically the pattern over time of blood pressure (ram Hg on the ordinate) in the fight hand side of the heart during one complete heart cycle. In particular, the solid line indicates the right ventricular pressure (RVP), while the dashed line and the dashed-and-dotted line indicate the pressure in the atrium and in the pulmonary artery, respectively. Points P1 and P2 identify the phase of isovolumetric contraction (CI), while points P3 and P4 identify the phase of isovolumetric relaxation (RI).
In FIG. 2, the signals 2a and 2b are operably coupled to analogdigital interface 3. The interface 3 transfers the signals supplied by the electrode 2a and the accelerometer 2b, converted into digital form, to the input of microprocessor 4. The latter constitutes, together with the respective memories, for instance of a ROM 5 and RAM 6, a control and processing system 7. Processing system 7 is the computing system of the device and operates to process the signals received (2a and 2b) according to the algorithm and programmed data stored in the memories. Its design is known to those of skill in the art. Associated with microprocessor 4 is clock 8 and output interface module 9 intended for driving, by means of corresponding output terminals 10, therapeutic device D. Bi-directional telemetric device 11 comprises receiver/transmitter interface 12 connected to the micro-processor 4, as well as radio-frequency transceiver 13, connected in bi-directional transmission to interface 12 and to transceiver antenna 14.
The process and control circuit 7 superintends all the operating phases of the device and processes the data coming from the adjacent interfaces. For this purpose, the ROM memory 5 serves preferentially as a program memory, while the RAM memory 6 serves preferentially as a memory for processing and maintaining the data programmed and saved by the microprocessor 4 itself, according to the processing carried out.
Transceiver 11 carries out the exchange of information between external programmer device 15 and control system 7. In particular, it performs the functions of receiving programmed parameters form outside and of transmitting the stored values to the RAM memory 6. Typically, the data transmitted regard the parameters processed by the system, measurements made or checks on the correctness of interaction between the external programmer and the implanted device itself. The transmission and receipt of data between the implantable device and the external programmer 15 takes place at radio frequencies. The processes referred to are achieved according to technical characteristics which are themselves well-known to those working in this sector.
Clock 8, which is also programmable, is able to supply the programming system with the time reference essential for a correct time base that refers to all the measurements.
Analog/digital interface 3 is typically equipped with a circuit for ventricular sensing which is able to recognize the electrical activity of the right ventricle and to discriminate it from interference coming from other sources, as well as with a circuit for amplification and analog-digital conversion of the signal of heart acceleration coming from the accelerometer located in the tip of the lead. This interface, therefore, sets in communication the endo cardial sensing lead and the acceleration sensor with the device for processing and controlling information 7. In particular, the device connected to the terminal 2a is built using the same technology utilized by current cardiac pacemakers and by PCDs for performing the same function, while the device connected to the terminal 2b is built as illustrated in U.S. Pat. No. 5,304,208.
The processing operations perforated by the system 7 on the signals coming from the terminals 2a and 2b have, in the first place, the purpose of analyzing the ECG signal (terminal 2a) in order to identify phases and/or events that are significant from the electrological point of view, for example, QRS and/or the T wave, measuring both amplitude and duration. Also sensed are parameters such as the frequency and period of the beat. All this is achieved on the basis of criteria which in themselves are known.
Starting from the analysis of the ECG signal, the system 7 processes the NHA(t) signal, isolating, within the signal, certain given time phases (segments) that constitute phases having an important haemodynamic meaning, for instance, isovolumetric contraction or isovolumetric relaxation, these being phases in which the dynamics of the heart wall is not perturbed by overall movements of the entire cardiac mass as a reaction to the ejection phases. For example, the control and processing system 7 is able to identify, in the context of the acceleration NHA(t), a segment t (see FIG. 3) immediately subsequent to the spontaneous QRS, within which the isovolumetric contraction phase occurs. In the presence of the cardiac pacing function, the system 7 identifies a segment (t+Δt, where Δt is of the order of approximately fifty msec) from the possible ventricular pacing spike, which contains the isovolumetric contraction phase. In the case where the segment corresponding to isovolumetric relaxation is isolated, the system 7 refers to the T wave of the ECG, both in the event of a spontaneous beat and in the presence of pacing.
The time duration of the segment t that is isolated is not necessarily fixed. For instance, in the case where the segment within which the isovolumetric contraction phase occurs is isolated, it is possible to configure the system 7 to vary the duration t, in order to associate with an increase in the beat rate (whether spontaneous or stimulated) a reduction, which may be even quite considerable, in this duration, or conversely, to associate with a reduction in the former an increase in the latter.
Another important function of endocardial ECG analysis is the recognition of specific arrhythmic events, for example, ventricular extrasystoles which, since they alter the normal mechanics of heart contractions, could lead to an inconect interpretation of the NHA signal. In this case, the identification of these events, based on the analysis of the ECG, makes it possible to exclude the mechanical effects of these anomalous events on the NHA signal from the subsequent processings. In the case of cardiac pacing, associating an effective NHA signal to the spike in the time interval set may enable the efficiency of the pacing to be ascertained.
The endocardial ECG signal may be processed not only for recognizing arrhythmias, but also for determining the pattern of heart rate, which is a very important parameter associated to NHA for evaluating the cardiac function. In particular, the system 7 proves able to evaluate the NHA/rate ratio, thus enabling identification of conditions of depression of the cardiac function in which to an increase in heart rate there corresponds an inadequate increase, or even a decrease in NHA. The availability of the ECG signal is moreover important for determining the so-called Heart Rate Variability (HRV) for measuring the sympathetic-vagal balance, as described in Patent No. EP-A-0 565 909.
On the NHA signal segments thus isolated, the system 7 can carry out the prescribed mathematical processing (calculation of peak-to-peak value, calculation of peak value, calculation of rectified mean value, or RMS, etc.).
In the control and processing system 7 are contained the decisionmaking mechanisms and the algorithms, obviously differentiated, which allow the application of a possible therapeutic phase whether of an electrical or of a pharmacological nature.
The output interface 9 transmits the command for intervention to the therapeutic device D, together with the values processed from the NHA and from the endocardial ECG, which are able to quantify the deviation from the optimal reference values, so allowing the device to intervene effectively.
In all due respect of the principle of the invention, the details and forms of implementation can be amply varied with regard to what has been described and illustrated above, without this entailing a departure from the sphere of the present invention.
|Patente citada||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US4936304 *||16 Dic 1987||26 Jun 1990||Thomas Jefferson University||Pacing system and method for cardiac pacing as a function of determined myocardial contractility|
|US5304208 *||20 May 1992||19 Abr 1994||Sorin Biomedica S.P.A.||Cardiostimulator device of the rate-responsive type|
|1||*||AAMI 17th Annual Meeting, May 9 12, 1982, San Francisco, An Interactive Microcomputer based Graphic System for Analysis of Cardio Dynamic Function .|
|2||AAMI 17th Annual Meeting, May 9-12, 1982, San Francisco, "An Interactive Microcomputer-based Graphic System for Analysis of Cardio-Dynamic Function".|
|3||American College of Surgeons, 1985, Surgical Forum, vol. XXXVI, Kresh et al., "Continuous Intraoperative Monitoring of Myocardial Tissue Pressure: Experimental & Clinical Results", pp. 301-303.|
|4||*||American College of Surgeons, 1985, Surgical Forum, vol. XXXVI, Kresh et al., Continuous Intraoperative Monitoring of Myocardial Tissue Pressure: Experimental & Clinical Results , pp. 301 303.|
|5||Heart Transplantation/vol. IV, No. 2, Feb. 1985, Organ Procurement & Organ Preservation, "The Intramyocardial Pressure", Kresh et al., pp. 241-264.|
|6||*||Heart Transplantation/vol. IV, No. 2, Feb. 1985, Organ Procurement & Organ Preservation, The Intramyocardial Pressure , Kresh et al., pp. 241 264.|
|7||Invited Speaker at 35th ACEMB Conference: Stimulation, Sensing, and Biocompatibility of Implanted Devices, Sep. 1982, "Pacing Sensors For Heart-Rate Control and Biophysical Telemetry", pp. 1-4.|
|8||*||Invited Speaker at 35th ACEMB Conference: Stimulation, Sensing, and Biocompatibility of Implanted Devices, Sep. 1982, Pacing Sensors For Heart Rate Control and Biophysical Telemetry , pp. 1 4.|
|9||Journal of Applied Physyiology, Mar. 1993, vol. 74, No. 3, "Ultrasonic Measurements In Vivo".|
|10||*||Journal of Applied Physyiology, Mar. 1993, vol. 74, No. 3, Ultrasonic Measurements In Vivo .|
|11||*||Progress in Artificial Organs 1983, Effects of Left Ventricular Bypass on Intramyocardial Mechanics , Kresh et al., pp. 107 116.|
|12||Progress in Artificial Organs-1983, "Effects of Left Ventricular Bypass on Intramyocardial Mechanics", Kresh et al., pp. 107-116.|
|13||*||Sensor Review, vol. 13, No. 1, 1993, pp. 22 25, MCB University Press, Canhui Cai et al., A Versatile Ultrasonic Ranging System .|
|14||Sensor Review, vol. 13, No. 1, 1993, pp. 22-25, MCB University Press, Canhui Cai et al., "A Versatile Ultrasonic Ranging System".|
|Patente citante||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US5941904 *||12 Sep 1997||24 Ago 1999||Sulzer Intermedics Inc.||Electromagnetic acceleration transducer for implantable medical device|
|US6077236 *||7 Jun 1994||20 Jun 2000||Cunningham; David||Apparatus for monitoring cardiac contractility|
|US6112116 *||22 Feb 1999||29 Ago 2000||Cathco, Inc.||Implantable responsive system for sensing and treating acute myocardial infarction|
|US6163721 *||9 Abr 1999||19 Dic 2000||Medtronic, Inc.||Power consumption reduction in medical devices by employing pipeline architecture|
|US6167303 *||9 Abr 1999||26 Dic 2000||Medtronic, Inc.||Power consumption reduction in medical devices employing just-in-time clock|
|US6185454||9 Abr 1999||6 Feb 2001||Medtronic, Inc.||Power consumption reduction in medical devices employing just-in-time voltage control|
|US6272379||17 Mar 1999||7 Ago 2001||Cathco, Inc.||Implantable electronic system with acute myocardial infarction detection and patient warning capabilities|
|US6289244||20 Ago 1999||11 Sep 2001||Cardiac Pacemakers, Inc.||Self audit system|
|US6400987||14 Jul 1998||4 Jun 2002||Sorin Biomedica Cardio S.P.A.||Active implantable device|
|US6409675||10 Nov 1999||25 Jun 2002||Pacesetter, Inc.||Extravascular hemodynamic monitor|
|US6480733||17 Dic 1999||12 Nov 2002||Pacesetter, Inc.||Method for monitoring heart failure|
|US6600949||5 May 2000||29 Jul 2003||Pacesetter, Inc.||Method for monitoring heart failure via respiratory patterns|
|US6741885||17 Jul 2001||25 May 2004||Pacesetter, Inc.||Implantable cardiac device for managing the progression of heart disease and method|
|US6763269||2 Nov 2001||13 Jul 2004||Pacesetter, Inc.||Frequency agile telemetry system for implantable medical device|
|US6766200||1 Nov 2001||20 Jul 2004||Pacesetter, Inc.||Magnetic coupling antennas for implantable medical devices|
|US6792308||15 Nov 2001||14 Sep 2004||Medtronic, Inc.||Myocardial performance assessment|
|US6842645||9 Nov 2001||11 Ene 2005||Pacesetter, Inc.||Presentation architecture for network supporting implantable cardiac therapy device|
|US6937899||30 Ago 2001||30 Ago 2005||Medtronic, Inc.||Ischemia detection|
|US6942622||29 Jul 2002||13 Sep 2005||Pacesetter, Inc.||Method for monitoring autonomic tone|
|US7010349||9 Dic 2003||7 Mar 2006||Cardiac Pacemakers, Inc.||System and method for detecting and displaying parameter interactions|
|US7047065||16 Oct 2003||16 May 2006||Cardiac Pacemakers, Inc.||System and method for correlation of patient health information and implant device data|
|US7174216||28 Ago 2003||6 Feb 2007||Pacesetter, Inc.||Notification system for implantable cardiac therapy devices|
|US7177700||27 Abr 2004||13 Feb 2007||Pacesetter, Inc.||Frequency agile telemetry system for implantable medical device|
|US7181268||25 Nov 2002||20 Feb 2007||Medtronic, Inc.||Ischemia detection|
|US7191006||5 Dic 2002||13 Mar 2007||Cardiac Pacemakers, Inc.||Cardiac rhythm management systems and methods for rule-illustrative parameter entry|
|US7225029||26 Oct 2001||29 May 2007||Pacesetter, Inc.||Implantable cardiac therapy device with dual chamber can to isolate high-frequency circuitry|
|US7470233 *||26 Ene 2005||30 Dic 2008||Medtronic, Inc.||Method and apparatus for muscle function measurement|
|US7526338||23 May 2005||28 Abr 2009||Pacesetter, Inc.||Implantable cardiac device for monitoring diastolic heart failure and method of operation and use thereof|
|US7613507||5 Jul 2006||3 Nov 2009||Ela Medical S.A.S.||Non-invasive detection of the occurrence of apneae or hypopneae in a patient|
|US7613672||27 Abr 2006||3 Nov 2009||Cardiac Pacemakers, Inc.||Medical device user interface automatically resolving interaction between programmable parameters|
|US7630770||24 Oct 2003||8 Dic 2009||Ela Medical S.A.S.||Management of respiratory pauses of hypopnea in an active implantable medical device of the cardiac pacemaker, defibrillator, cardiovertor or multisite device type|
|US7662103 *||21 Dic 2005||16 Feb 2010||Ela Medical S.A.S.||Apparatus for non-invasive diagnosis of vasovagal syncope in a patient|
|US7664547||21 Jun 2006||16 Feb 2010||Ela Medical S.A.S.||Active implantable medical device with biventricular pacing and automatic optimization of pacing configuration|
|US7751892||6 May 2004||6 Jul 2010||Cardiac Pacemakers, Inc.||Implantable medical device programming apparatus having a graphical user interface|
|US7792574||15 Jun 2007||7 Sep 2010||Ela Medical S.A.S.||Alert predictive of degredation of a patient's clinical status for an active implantable medical device as for pacing, resynchronization, defibrillation and/or cardioversion|
|US7801596||17 May 2005||21 Sep 2010||Angel Medical Systems, Inc.||Physician's programmer for implantable devices having cardiac diagnostic and patient alerting capabilities|
|US7844322||24 Abr 2006||30 Nov 2010||Cardiac Pacemakers, Inc.||System and method for correlation of patient health information and implant device data|
|US7848792||5 Jul 2006||7 Dic 2010||Ela Medical S.A.S.||Detection of apneae and hypopneae in an active implantable medical device|
|US7962203||29 Dic 2003||14 Jun 2011||Cardiac Pacemakers, Inc.||Arrhythmia display|
|US7966068||18 May 2007||21 Jun 2011||Ela Medical S.A.S.||Detecting a lead fracture in an active implantable medical device for cardiac pacing resynchronization cardioversion and/or defibrillation|
|US8002701||12 Mar 2007||23 Ago 2011||Angel Medical Systems, Inc.||Medical alarm and communication system and methods|
|US8046060||14 Nov 2005||25 Oct 2011||Cardiac Pacemakers, Inc.||Differentiating arrhythmic events having different origins|
|US8118751||2 Mar 2009||21 Feb 2012||Cardiosync, Inc.||Devices and methods for accelerometer-based characterization of cardiac function and identification of LV target pacing zones|
|US8121689||1 Oct 2007||21 Feb 2012||Cardiac Pacemakers, Inc.||Proactive interactive limits override for implantable medical device user interface|
|US8126555||25 Ene 2009||28 Feb 2012||Ela Medical S.A.S.||Bidirectional communications between a generator and sensors or actuators of a lead for an active implantable medical device|
|US8131351||8 Nov 2010||6 Mar 2012||Cardiac Pacemakers, Inc.||System and method for correlation of patient health information and implant device data|
|US8175715||20 Dic 2006||8 May 2012||Pacesetter, Inc.||Frequency agile telemetry system for implantable medical device|
|US8195293||18 May 2007||5 Jun 2012||Sorin Crm S.A.S||Detecting ventricular noise artifacts in an active implantable medical device for pacing, resynchronization and/or defibrillation of the heart|
|US8321366||7 Jul 2011||27 Nov 2012||Cardiac Pacemakers, Inc.||Systems and methods for automatically resolving interaction between programmable parameters|
|US8433396||18 Abr 2003||30 Abr 2013||Medtronic, Inc.||Methods and apparatus for atrioventricular search|
|US8463369||13 Jun 2011||11 Jun 2013||Cardiac Pacemakers, Inc.||Arrhythmia display|
|US8494629||17 Feb 2011||23 Jul 2013||Sorin Crm S.A.S.||Apparatus and method for automatic optimization of atrioventricular delay for an active medical device|
|US8548576||2 Mar 2012||1 Oct 2013||Cardiac Pacemakers, Inc.||System and method for correlation of patient health information and implant device data|
|US8554313||19 Feb 2009||8 Oct 2013||Sorin Crm S.A.S.||Device for the analysis of an endocardiac signal of acceleration|
|US8738560||6 Nov 2012||27 May 2014||Cardiac Pacemakers, Inc.||Systems and methods for automatically resolving interaction between programmable parameters|
|US8781566||12 Feb 2008||15 Jul 2014||Angel Medical Systems, Inc.||System and methods for sliding-scale cardiac event detection|
|US8805486||4 Oct 2013||12 Ago 2014||Sorin Crm S.A.S.||Device for the analysis of an endocardiac signal of acceleration|
|US8831705||12 Sep 2011||9 Sep 2014||Cardiosync, Inc.||Devices and method for accelerometer-based characterization of cardiac synchrony and dyssynchrony|
|US8838215||27 Feb 2007||16 Sep 2014||Angel Medical Systems, Inc.||Systems and methods of medical monitoring according to patient state|
|US8838220||12 Ago 2013||16 Sep 2014||Cardiac Pacemakers, Inc.||System and method for correlation of patient health information and implant device data|
|US8870797||11 Ene 2010||28 Oct 2014||Norman A. Paradis||Non-invasive device for synchronizing chest compression and ventilation parameters to residual myocardial activity during cardiopulmonary resuscitation|
|US8874209||9 Dic 2008||28 Oct 2014||Sorin Crm S.A.S.||Device for characterizing the cardiac status of a patient equipped with a biventricular pacing active implant|
|US8874210||11 Jun 2010||28 Oct 2014||Sorin Crm Sas||Apparatus and method for analyzing patient tolerance to a stimulation mode favoring a spontaneous atrioventricular conduction|
|US9155904||9 Sep 2014||13 Oct 2015||Cardiac Pacemakers, Inc.||System and method for correlation of patient health information and implant device data|
|US9205267||22 Jul 2013||8 Dic 2015||Sorin Crm S.A.S.||Apparatus and method for automatic optimization of atrioventricular delay for an active medical device|
|US9259543 *||14 Jul 2011||16 Feb 2016||Zoll Medical Corporation||Non-invasive device for synchronizing chest compression and ventilation parameters to residual myocardial activity during cardiopulmonary resuscitation|
|US9452292||25 Abr 2014||27 Sep 2016||Medtronic, Inc.||Method and apparatus for detecting loss of capture|
|US9504835||9 Sep 2014||29 Nov 2016||Sorin Crm Sas||Stimulation mode determination|
|US9533166||9 Oct 2015||3 Ene 2017||Cardiac Pacemakers, Inc.||System and method for correlation of patient health information and device data|
|US20030158492 *||25 Nov 2002||21 Ago 2003||Sheldon Todd J.||Ischemia detection|
|US20040082976 *||16 Oct 2003||29 Abr 2004||Cardiac Pacemakers, Inc.||System and method for correlation of patient health information and implant device data|
|US20040111131 *||5 Dic 2002||10 Jun 2004||Bo Hu||Cardiac rhythm management systems and methods for rule-illustrative parameter entry|
|US20040138718 *||24 Oct 2003||15 Jul 2004||Marcel Limousin||Management of respiratory pauses of hypopnea in an active implantable medical device of the cardiac pacemaker, defibrillator, cardiovertor or multisite device type|
|US20040143306 *||29 Dic 2003||22 Jul 2004||Cardiac Pacemakers. Inc.||Arrhythmia display|
|US20040215262 *||18 Abr 2003||28 Oct 2004||Bozidar Ferek-Petric||Methods and apparatus for atrioventricular search|
|US20050033385 *||6 May 2004||10 Feb 2005||Peterson Les Norman||Implantable medical device programming apparatus having a graphical user interface|
|US20050113886 *||23 Nov 2004||26 May 2005||Fischell David R.||Implantable medical system with long range telemetry|
|US20050209649 *||17 Mar 2004||22 Sep 2005||Bozidar Ferek-Petric||Mechanical sensing system for cardiac pacing and/or for cardiac resynchronization therapy|
|US20060167358 *||26 Ene 2005||27 Jul 2006||Mustafa Karamanoglu||Method and apparatus for muscle function measurement|
|US20060178586 *||23 Dic 2005||10 Ago 2006||Dobak John D Iii||Devices and methods for accelerometer-based characterization of cardiac function and identification of LV target pacing zones|
|US20060189874 *||21 Dic 2005||24 Ago 2006||Ela Medical, S.A.||Apparatus for non-invasive diagnosis of vasovagal syncope in a patient|
|US20060265020 *||17 May 2005||23 Nov 2006||Fischell David R||Physician's programmer for implantable devices having cardiac diagnostic and patient alerting capabilities|
|US20060293715 *||21 Jun 2006||28 Dic 2006||Ela Medical S.A.S.||Active implantable medical device with biventricular pacing and automatic optimization of pacing configuration|
|US20070016089 *||15 Jul 2005||18 Ene 2007||Fischell David R||Implantable device for vital signs monitoring|
|US20070100384 *||8 Dic 2006||3 May 2007||Fischell David R||Implantable medical system with long range telemetry|
|US20070156059 *||5 Jul 2006||5 Jul 2007||Ela Medical S.A.S||detection of apneae and hypopneae in an active implantable medical device|
|US20070167851 *||5 Jul 2006||19 Jul 2007||Ela Medical S.A.S||Non-invasive detection of the occurrence of apneae or hypopneae in a patient|
|US20070208263 *||27 Feb 2007||6 Sep 2007||Michael Sasha John||Systems and methods of medical monitoring according to patient state|
|US20070270914 *||18 May 2007||22 Nov 2007||Ela Medical S.A.S.||Detecting a lead fracture in an active implantable medical device for cardiac pacing resynchronization cardioversion and/or defibrillation|
|US20070282379 *||18 May 2007||6 Dic 2007||Ela Medical S.A.S.||Detecting ventricular noise artifacts in an active implantable medical device for pacing, resynchronization and/or defibrillation of the heart|
|US20070293736 *||15 Jun 2007||20 Dic 2007||Ela Medical S.A.S.||Alert Predictive Of Degredation Of A Patient's Clinical Status For an Active Implantable Medical Device As For Pacing, Resynchronization, Defibrillation And/Or Cardioversion|
|US20080126968 *||27 Abr 2006||29 May 2008||Jeff West||Medical device user interface automatically resolving interaction between programmable parameters|
|US20080188762 *||12 Feb 2008||7 Ago 2008||Michael Sasha John||Systems and methods for cardiac segmentation analysis|
|US20080188763 *||12 Feb 2008||7 Ago 2008||Michael Sasha John||System and methods for sliding-scale cardiac event detection|
|US20090157134 *||9 Dic 2008||18 Jun 2009||Filippo Ziglio||Device For Characterizing the Cardiac Status Of A Patient Equipped With A Biventricular Pacing Active Implant|
|US20090192572 *||25 Ene 2009||30 Jul 2009||Ela Medical S.A.S.||Bidirectional Communications Between A Generator And Sensors Or Actuators Of A Lead For An Active Implantable Medical Device|
|US20090209875 *||19 Feb 2009||20 Ago 2009||Ela Medical S.A.S.||Device for the analysis of an endocardiac signal of acceleration|
|US20090306736 *||17 Dic 2008||10 Dic 2009||Dobak Iii John D||Accelerometer-based monitoring of the frequency dynamics of the isovolumic contraction phase and pathologic cardiac vibrations|
|US20100049063 *||2 Mar 2009||25 Feb 2010||Dobak Iii John D||Devices and methods for accelerometer-based characterization of cardiac function and identification of lv target pacing zones|
|US20100114220 *||11 Ene 2010||6 May 2010||Norman A. Paradis||Non-invasive device for synchronizing chest compression and ventilation parameters to residual myocardial activity during cardiopulmonary resuscitation|
|US20100249868 *||9 Jun 2010||30 Sep 2010||Les Norman Peterson||Implantable medical device programming apparatus having a graphical user interface|
|US20100318150 *||11 Jun 2010||16 Dic 2010||Sorin Crm S.A.S.||Apparatus And Method For Analyzing Patient Tolerance To A Stimulation Mode Favoring A Spontaneous Atrioventricular Conduction|
|US20110046692 *||8 Nov 2010||24 Feb 2011||James Kalgren||System and method for correlation of patient health information and implant device data|
|US20110202099 *||17 Feb 2011||18 Ago 2011||Sorin Crm S.A.S.||Apparatus and method for automatic optimization of atrioventricular delay for an active medical device|
|US20120016179 *||14 Jul 2011||19 Ene 2012||Paradis Norman|
|EP0896828A2||12 Ago 1998||17 Feb 1999||SORIN BIOMEDICA S.p.A.||An active implantable patient monitoring device|
|EP1023916A1||28 Ene 1999||2 Ago 2000||SORIN BIOMEDICA CARDIO S.p.A.||Implantable cardiostimulation apparatus|
|EP1151718A2||30 Abr 2001||7 Nov 2001||Pacesetter, Inc.||Apparatus for monitoring heart failure via respiratory patterns|
|EP1151719A2||30 Abr 2001||7 Nov 2001||Pacesetter, Inc.||Apparatus for monitoring heart failure via respiratory patterns|
|EP1302156A2||16 Oct 2002||16 Abr 2003||Pacesetter, Inc.||Assessing heart failure status using morphology of a signal representative of arterial pulse pressure|
|Clasificación de EE.UU.||607/17, 600/515, 607/6|
|Clasificación internacional||A61N1/365, A61N1/37|
|Clasificación cooperativa||A61N1/3702, A61N1/36542, A61N1/365|
|Clasificación europea||A61N1/37B, A61N1/365B6, A61N1/365|
|24 Feb 1995||AS||Assignment|
Owner name: SORIN BIOMEDICA S.P.A.
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:PLICCHI, GIANNI;CORBUCCI, GIORGIO;REEL/FRAME:007411/0765
Effective date: 19950203
|3 Jul 1995||AS||Assignment|
Owner name: SORIN BIOMEDICA S.P.A., ITALY
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:PLICCHI, GIANNI;CORBUCCI, GIORGIO;REEL/FRAME:007571/0471
Effective date: 19950203
|9 Sep 1997||CC||Certificate of correction|
|31 Ago 1999||FPAY||Fee payment|
Year of fee payment: 4
|12 Ago 2003||FPAY||Fee payment|
Year of fee payment: 8
|10 Ago 2007||FPAY||Fee payment|
Year of fee payment: 12